Dual antenna microwave resection and ablation device, system and method of use

ABSTRACT

A system for generating microwave energy includes a microwave generator that generates first and second microwave signals, a transmission line and a dual antenna microwave device. The transmission line transmits the first and second microwave signals to the microwave device. The microwave device includes a first antenna proximal a second antenna and a dual-sided choke positioned therebetween. The first antenna receives the first microwave signal from the transmission line between a first conductor and a second conductor and the second antenna receives the second microwave signal between the second conductor and a third conductor. The dual-sided choke includes a first and a second antenna choke circuit. The first antenna choke circuit limits the propagation of electromagnetic fields generated by the first antenna toward the second antenna and the second antenna choke circuit limits the propagation of electromagnetic fields generated by the second antenna toward the first antenna.

CROSS-REFERENCE TO RELATED APPLICATION

This application is a continuation application of U.S. patent application Ser. No. 13/020,664, filed on Feb. 3, 2011, the entire contents of which are incorporated by reference herein.

BACKGROUND

1. Technical Field

This application is a continuation application of U.S. patent application Ser. No. 13/020,664, filed on Feb. 3, 2011, now U.S. Pat. No. 9,028,476, the entire contents of which are incorporated by reference herein.

2. Description of Related Art

In the treatment of diseases such as cancer, certain types of cancer cells have been found to denature at elevated temperatures (which are slightly lower than temperatures normally injurious to healthy cells.) These types of treatments, known generally as hyperthermia therapy, typically utilize electromagnetic radiation to heat diseased cells to temperatures above 41° C., while maintaining adjacent healthy cells at lower temperatures where irreversible cell destruction will not occur. Other procedures utilizing electromagnetic radiation to heat tissue also include ablation and coagulation of the tissue. Such microwave ablation procedures, e.g., such as those performed for menorrhagia, are typically done to ablate and coagulate the targeted tissue to denature or kill the tissue. Many procedures and types of devices utilizing electromagnetic radiation therapy are known in the art. Such microwave therapy is typically used in the treatment of tissue and organs such as the prostate, heart, liver, lung, kidney, and breast.

Presently, there are several types of microwave probes in use, e.g., monopole, dipole, and helical. A monopole antenna probe consists of a single, elongated microwave conductor exposed at the end of the probe. The probe is typically surrounded by a dielectric sleeve. A dipole antenna consists of a coaxial construction having an inner conductor and an outer conductor with a dielectric junction separating a portion of the inner conductor. The inner conductor may be coupled to a portion corresponding to a first dipole radiating portion, and a portion of the outer conductor may be coupled to a second dipole radiating portion. The dipole radiating portions may be configured such that one radiating portion is located proximally of the dielectric junction, and the other portion is located distally of the dielectric junction. In the monopole and dipole antenna probes, microwave energy generally radiates perpendicularly from the axis of the conductor.

The typical microwave antenna has a long, thin inner conductor that extends along the axis of the probe and is surrounded by a dielectric material and is further surrounded by an outer conductor around the dielectric material such that the outer conductor also extends along the axis of the probe.

In the case of tissue ablation, a high radio frequency electrical current in the range of about 500 MHz to about 10 GHz is applied to a targeted tissue site to create an ablation volume, which may have a particular size and shape. The ablation volume is correlated to antenna design, antenna performance, antenna impedance and tissue impedance. The particular type of tissue ablation procedure may dictate a particular ablation volume in order to achieve a desired surgical outcome. By way of example, and without limitation, a spinal ablation procedure may call for a longer, narrower ablation volume, whereas in a prostate ablation procedure, a more spherical ablation volume may be required.

One particular ablation procedures is a tissue resection procedure. In a tissue resection procedure a clinician first determines that portion of a particular organ, containing unhealthy tissue needs to be resected or removed. A resection line is positioned on the organ, between the unhealthy tissue and the healthy tissue, such that when the tissue along the resection line is ablated, the unhealthy portion may be removed while leaving a sufficient portion of the organ in a viable or functional manor.

One step in a microwave resection or ablation procedure is the step of placing one or more microwave energy delivery device in a portion of target tissue. The placement step is a critical step because proper placement often depends on several factors including the size and shape of the desired ablation region, the type of ablation device (or devices) used, the parameters of the microwave energy signal (i.e., frequency, power, duty-cycle, etc.) and the predicted ablation size that the ablation device may generate.

The placement step becomes even more complicated when the procedure requires a plurality of ablation devices. For example, a resection procedure, which requires the ablation of tissue along a predefined resection line, often requires the placement of a plurality of microwave energy delivery devices along a particular resection line. One particular method of placement includes the insertion of a plurality of tissue penetrating microwave energy delivery devices that are positioned in the target tissue by percutaneous insertion.

In a resection procedure, once the location of the resection line has been determined, the clinician then determines an arrangement of ablation devices that will ablate the tissue along the resection line. This arrangement is typically determined by the predicted ablation region size and shape for the selected ablation device or devices. In most resection procedures a plurality of ablation devices are positioned along the resection line in order to deliver a sufficient amount of energy to achieve complete ablation of the tissue along the resection line.

In one known resection method ablation, the resection is performed by performing a first ablation along a resection line, repositioning the ablation device to a subsequent position along the resection line and performing a subsequent ablation. This step is repeated along the resection line until the entire resection line is ablated. In another resection method, a plurality of ablation devices are inserted along a resection line and the plurality of devices are simultaneously energized (or nearly simultaneously energized) to ablate the tissue along the resection line. While both methods are effective, the first method is time consuming because a plurality of ablations are performed in sequence. The second method requires precise placement of the plurality of devices to insure complete ablation with minimal interaction or interference between adjacent devices.

Regardless of the method used, resection procedures are complicated because the desired ablation region for a typical resection procedure is much different in shape and size than the desired ablation region for a typical ablation procedure. The target tissue in an ablation procedure is typically a tumorous mass that is usually circular, elliptical or oblong. As such, microwave ablation devices have typically been design to generate round, oblong or egg-shaped ablation regions. In contrast to an ablation procedure, a resection procedure typically requires ablation of an elongated region of tissue along the resection line, wherein the length of the ablation region in a resection procedure is typically much greater than the width and/or thickness of the ablation region generated by a typical ablation device.

The difference in shape of the desired ablation region becomes problematic because a clinician typically uses the same ablation device for ablation procedures and resection procedure.

SUMMARY

The present disclosure describes a dual antenna microwave resection and ablation device configured to generate ablation regions of desirable size and dimension for ablation procedures and resection procedures.

One embodiment of the present disclosure relates to a system for generating microwave energy having a microwave generator and a transmission line that connects to a dual antenna microwave device. The microwave generator generates a first and second microwave signals that are transmitted to the dual antenna microwave device by the transmission line. The dual antenna microwave device includes a first antenna, a second antenna distal of the first antenna and a dual-sided choke positioned between the first antenna and the second antenna. The first antenna receives the first microwave frequency signal from the transmission line between a first conductor and a second conductor of the transmission line and the second antenna receives the second microwave frequency signal from the second conductor and a third conductor of the transmission line. The dual-sided choke includes a choke conductor that further includes a first antenna choke circuit and a second antenna choke circuit. The first antenna choke circuit is configured to limit the propagation of electromagnetic fields generated by the first antenna toward the second antenna and the second antenna choke circuit is configured to limit the propagation of electromagnetic fields generated by the second antenna toward the first antenna. In one embodiment the choke conductor electrically connects to the second conductor.

The length of the first antenna, the second antenna and/or the dual-sided choke may be related to one-quarter wavelength of the first microwave frequency signal and/or the second microwave frequency signal. The first antenna and the second antenna may be configured to simultaneously radiate the first and second microwave frequency signals, respectively. A dielectric coating may be disposed at least partially over the first antenna, the second antenna and/or the dual-sided choke.

The first antenna may further include a distal radiating section and the second antenna may further include a proximal radiating section, wherein the first antenna and the second antenna generate electromagnetic fields between the distal radiating section of the first antenna and the proximal radiating section of the second antenna. The proximal radiating section and the distal radiating section may have a length proportional to an effective wavelength of the radiation transmitted by the antenna assembly.

In a further embodiment, the dual antenna microwave device further includes a feedline having an inner conductor, an outer conductor and a triaxial conductor. At least a portion of the feedline includes the inner conductor, the outer conductor and the triaxial conductor in a triaxial orientation.

The first antenna may further include a first feedpoint and the second antenna may further include a second feedpoint. The distance between the midpoint of the first feedpoint and the midpoint of the second feedpoint may be related to a quarter wavelength of at least one of the first and second microwave frequency signals.

In a further embodiment, the first antenna choke circuit and/or the length of the second antenna choke circuit may be related to a quarter wavelength of the first microwave frequency signal and/or the second microwave frequency signal.

Another embodiment of the present disclosure is a device for ablating tissue, including a transmission line, a first antenna, a second antenna and a dual-sided choke. The second antenna is distal the first antenna and the dual-sided choke is positioned between the first antenna and the second antenna. The transmission line connects the device to a microwave energy source and transmits a first and a second microwave frequency signal from the microwave energy source to the first and second antennas. The first antenna receives the first microwave frequency signal between a first conductor and a second conductor of the transmission line and the second antenna receives the second microwave frequency signal between the second conductor and a third conductor of the transmission line. The dual-sided choke includes a choke conductor that further includes a first antenna choke circuit and a second antenna choke circuit. The first antenna choke circuit is configured to limit the propagation of electromagnetic fields generated by the first antenna toward the second antenna and the second antenna choke circuit is configured to limit the propagation of electromagnetic fields generated by the second antenna toward the first antenna.

Yet another embodiment of the present disclosure relates to a microwave antenna assembly for applying microwave energy therapy, including a proximal portion having an inner conductor, an outer conductor and a triaxial conductor each extending therethrough. The assembly also includes a first antenna, a second antenna and a dual-sided choke. In the proximal portion the inner conductor is disposed within the outer conductor and the outer conductor is disposed within the triaxial conductor. The first antenna includes a first antenna distal radiating section that connects to the triaxial conductor and a first antenna proximal radiating section that connects to the outer conductor. The second antenna includes a second antenna distal radiating section that connects to the inner conductor and a second antenna proximal radiating section that connects to the inner conductor. The dual-sided choke, having at least a portion therewith disposed between the first antenna and the second antenna, includes a first antenna choke circuit and a second antenna choke circuit. The first antenna choke circuit is configured to limit the propagation of electromagnetic fields generated by the first antenna toward the second antenna and the second antenna choke circuit is configured to limit the propagation of electromagnetic fields generated by the second antenna toward the first antenna

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A is a schematically-illustrated view of a microwave energy delivery system including a dual antenna microwave resection and ablation device (DAMRAD) in accordance with one embodiment of the present disclosure;

FIG. 1B is a schematically-illustrated view of a microwave energy delivery system including first and second microwave signal generators that provide first and second microwave energy signals to a DAMRAD in accordance with another embodiment of the present disclosure.

FIG. 2 is a graphical illustration of a simulated power flow generated by the distal antenna of the DAMRAD;

FIG. 3 is a graphical illustration of a simulated power flow generated by the proximal antenna of the DAMRAD;

FIG. 4 is a graphical illustration of a simulated power flow generated by the distal and proximal antennas of the DAMRAD;

FIG. 5 is a cross-sectional illustration of the antenna portion of the DAMRAD;

FIG. 6 is a cross-sectional illustration of the distal antenna of the DAMRAD;

FIG. 7 is a cross-sectional illustration of the proximal antenna of the DAMRAD;

FIG. 8 is a cross-sectional illustration of the dual-sided choke of the DAMRAD in accordance with another embodiment of the present disclosure

FIG. 9 is a cross-sectional illustration of a double-sided choke of the DAMRAD in accordance with yet another embodiment of the present disclosure.

DETAILED DESCRIPTION

Detailed embodiments of the present disclosure are described herein; however, it is to be understood that the disclosed embodiments are merely examples and may be embodied in various forms. Therefore, specific structural and functional details disclosed herein are not to be interpreted as limiting, but merely as a basis for the claims and as a representative basis for teaching one skilled in the art to variously employ the present disclosure in virtually any appropriately detailed structure.

Referring to FIG. 1A, a microwave energy delivery system 10 is shown including a microwave generator 100, a dual antenna microwave resection and ablation device (DAMRAD) 110 employing embodiments of the present disclosure and a triaxial transmission cable 120 connected therebetween. Triaxial transmission cable 120 may be permanently affixed to the DAMRAD 110 (as illustrated in FIG. 1A) or triaxial transmission cable 120 may be separate from the DAMRAD 110. Alternatively, DAMRAD 110 may connect to a plurality of coaxial transmission cables (not explicitly shown) each of the plurality of coaxial transmission cables providing a microwave energy signal to the DAMRAD 110. The microwave energy signals provided to the triaxial transmission cable 120 or to the plurality of coaxial transmission cables may be in-phase or out-of-phase with respect to each other. In one embodiment, the microwave generator 100 may further include a microwave signal splitter (not explicitly shown) configured to divide a single microwave energy signal, generated by the microwave generator 100, into two signals for the DAMRAD 110.

As illustrated in FIG. 1A, DAMRAD 110 includes a percutaneous device having a sharpened tip 118 configured to penetrate tissue. The antenna portion 116 includes a proximal antenna 116 a and a distal antenna 116 b separated by a dual-sided choke 128. The handle 112 is connected to the antenna portion 116 by an elongated shaft 114.

Elongated shaft 114 is configured to provide a microwave energy signal to the proximal and distal antennas 116 a, 116 b respectively. In one embodiment the elongated shaft 114 includes three conductors arranged in a triaxial configuration thereby forming a triaxial transmission line. Alternatively, elongated shaft 114 may include a plurality of transmission lines each supplying a microwave energy signal to one of the antennas 116 a, 116 b.

Microwave generator 100 is configured to provide suitable microwave energy signals to the DAMRAD 110. The microwave energy signals may be substantially identical or may be related in one or more ways (e.g., in-phase, similar frequency and/or power level). For example, microwave generator 100 may include a phase-shifting circuit (not explicitly shown) configured to offset the first and second microwave signals at a predetermined microwave frequency by a selected phase shift. The selected phase shift may be determined by the clinician, by a physical property or configuration of the DAMRAD 116 or may be selected based on feedback (i.e., reflected energy) measured by the microwave generator 100.

Microwave generator may also include first and second microwave signal generating circuits (not explicitly shown) that generate a first microwave signal at a first frequency and a second microwave signal at a second frequency, wherein the first and second frequencies are not the same. In one embodiment, the first and second frequencies are harmonics.

Referring to FIG. 1B, a microwave energy delivery system 11 is shown including a first microwave generator 100 a and a second microwave generator 100 b connected to a DAMRAD 100 through a coaxial-to-triaxial connector 105. First microwave generator 100 a generates a first microwave energy signal and second microwave generator 100 b generates a second microwave signal. The first and second microwave signals are provided to the coaxial-to-triaxial connector 105 through first and second coaxial cables 120 a, 120 b, respectively, connected to the first and second coaxial connectors 105 a, 105 b. Triaxial connector 105 passes the first and second microwave energy signals to the triaxial cable 120 connected to the DAMRAD 100. First and second microwave generators 100 a, 100 b may connect to each other through a microwave generator interface cable 107 and provide control and/or synchronization information therebetween.

The first and second microwave signals generated by the first and second microwave generators 100 a, 100 b may be substantially identical or may be related in one or more ways (e.g., in-phase, similar frequency and/or power level). For example, first microwave signal generated by first microwave generator 100 a may be shifted in phase with respect to the second microwave signal generated by second microwave generator 100 b. Microwave generator interface cable 107 may provide one or more parameters related to one of the first or second microwave signals. For example, microwave generator interface cable 107 may provide signal phase data, a timing signal or frequency data between the first and second generators 100 a, 100 b. Microwave interface cable 107 may provide a sample of, or signal related to, one of the first and/or second microwave signals.

The phase shift between the first and the second microwave signals may be determined by the clinician, by a physical property or configuration of the DAMRAD 116 or may be selected based on feedback (i.e., reflected energy) measured by the microwave generator 100.

The DAMRAD may be designed to operate at microwave frequencies of 915 MHz, 2.45 GHz or any other suitable frequency. A DAMRAD designed to operate at 915 MHz, as compared to a DAMRAD designed to operate at 2.45 GHz, would include longer antenna lengths (due to the longer wavelength) and therefore would produce longer ablation regions, as described hereinbelow.

The energy associated with fields generated by a microwave antenna may be represented as electric field strengths (hereinafter, E-field) or by magnetic field strengths (hereinafter, H-field), wherein each provide equally valid expressions of radiant energy flow. The simulated power flows 236, 336, 436 in FIGS. 2-4 illustrates power flow as the product of the E-field (in V/m) and H-field (in A/m) wherein the units of the product of the E-field and the H-field yields VA/m². The simulations in FIGS. 2-4 were performed with a 0.915 GHz microwave energy signal provided to the distal antenna 116 b in FIG. 2, the proximal antenna 116 a in FIG. 3 and the proximal and distal antennas 116 a, 116 b in FIG. 4.

The simulated power flows 236, 336, 436, for simplicity, are illustrated as three distinct areas of power flow. For example, as illustrated in FIG. 2 the simulated power flow 236 includes an area of high density power flow 236 a, an area of medium density power flow 236 b and an area of low density power flow 236 c. It is understood that an actual and/or simulated power flow 236, 336, 436 may include a power flow gradient with the absolute magnitude of the power flow 236 being proportionally decreasing (linearly, non-linearly or exponentially) and related to the distance from the distal antenna 116 b.

FIG. 2 is a graphical illustration of a simulated power flow 236 generated by the distal antenna 116 b of the DAMRAD 110 (for illustrative purpose the DAMRAD 110 is superimposed on the graphical illustration). The DAMRAD 110 includes a distal antenna 116 b a proximal antenna 116 a separated by a dual-sided choke 128. The simulation was performed with a 915 MHz microwave energy signal provided to the distal antenna 216 b. The proximal portion 236 d of the power flow 236 is shunted by the distal side of the dual-sided choke 128 as discussed hereinbelow.

FIG. 3 is a graphical illustration of a simulated power flow 336 generated by the proximal antenna 116 a of the DAMRAD 110 (for illustrative purposes the DAMRAD 110 is superimposed on the graphical illustration). For simplicity, the simulated power flow 336 is illustrated to include an area of high density power flow 336 a, an area of medium density power flow 336 b and an area of low density power flow 336 c. The distal portion 336 e of the power flow 336 is shunted by a proximal side of the dual-sided choke 128 as discussed hereinbelow. Since the proximal side of the proximal antenna 116 a is unchoked, the proximal portion 336 f of the power flow 336 extends beyond the proximal end of the proximal antenna 116 a.

FIG. 4 is a graphical illustration of a simulation of the combined power flow 436 generated by the distal and proximal antennas 116 b, 116 a of the DAMRAD 110 (for illustrative purposes the DAMRAD 110 is superimposed on the graphical illustration). The simulated power flow 436 includes an area of high density power flow 436 a, an area of medium density power flow 436 b and an area of low density power flow 436 c. The dual-sided choke 128 shunts the magnetic fields generated on the proximal portion of the distal antenna 116 b and shunts the magnetic fields generated on the distal portion of the proximal antenna 116 a. As such, there is little interaction between the magnetic fields generated by either antenna 116 a, 116 b in the area adjacent the dual-sided choke 128. Since the proximal side of the proximal antenna 116 a is unchoked, the proximal portion 436 f of the power flow 436 extends beyond the proximal end of the proximal antenna 116 a.

The area adjacent and/or surrounding the dual-sided choke 128 of the DAMRAD 110 receives energy from the electromagnetic fields generated by the distal antenna 116 b and from electromagnetic fields generated by the proximal antenna 116 a thereby creating a synergistic heating effect in this region. It can be ascertained from the simulated power flows 236, 336, 436 illustrated in FIGS. 2-4 that the DAMRAD 110 is configured to generate an elongated region of high density power flow 436 a that extends from the distal tip 118 of the DAMRAD 110 to a point proximal the proximal antenna 116 a. As such, the effective length of the ablation region that may be generated from the DAMRAD 110 is at least two times and up to three times the length of an ablation region generated from a microwave energy delivery device including a single antenna.

A synergistic heating effect in the region surround the dual-sided choke 128 may be obtained by either simultaneous energy delivery to the dual antennas 116 a, 116 b or by alternating the delivery of the microwave energy signal between the proximal antenna 116 a and the distal antenna 116 b or any combination thereof. As will be discussed hereinbelow and illustrated in FIG. 1, in at least one embodiment the microwave signals provided to the proximal antenna 116 a and the distal antenna 116 b are provided from the same microwave generator 100 and the triaxial transmission cable 120. As such, the microwave signals provided to the proximal antenna 116 a and the distal antenna 116 b share substantially identical supply paths and distances. As such, the microwave energy signals provided to the two antennas 116 a, 116 b are inherently in-phase with respect to each other.

As illustrated in FIGS. 2-4, the DAMRAD 110 is configured to generate ablation regions of varying sizes and shapes. The DAMRAD 110 may be utilized in a manner similar to that of a standard ablation device by utilizing and energizing only one of the dipole antennas 116 a, 116 b. Alternatively, in another embodiment the distal antenna 116 b may be utilized to generate a typical ablation region and the proximal antenna 116 a may be utilized to selectively ablate at least a portion of the insertion path. Finally, as illustrated in FIG. 4, the DAMRAD 110 is configured to generate elongated ablation region with a shape that is particularly suited for resection procedures.

FIG. 5 is a cross-sectional illustration of the antenna portion 116 of the DAMRAD 110 of FIG. 1. The antenna portion 116 includes the proximal antenna 116 a, the distal antenna 116 b separated by the dual-sided choke 128. Distal the distal antenna 116 b is the sharpened tip 118 configured to facilitate percutaneous insertion of the DAMRAD 110 into patient tissue (not explicitly shown). The distal antenna 116 b, the proximal antenna 116 a and the dual-sided choke 128 are further illustrated in FIG. 6, FIG. 7 and FIG. 8, respectively, and are described in detail hereinbelow.

FIG. 6 is a cross-sectional illustration of the distal antenna 116 b of the DAMRAD 110 of FIG. 5. The distal antenna 116 b is configured as a dipole antenna and includes a distal antenna distal radiating section 117 and a distal antenna proximal radiating section 115, both of which receive a microwave energy signal from the distal antenna feedpoint 119 b at the distal end of the internal coaxial cable 120 a. The internal coaxial cable 120 a includes an inner conductor 121 and an outer conductor 123 in a coaxial arrangement and separated by an inner dielectric 122 and provides the microwave energy signal to the distal antenna feedpoint 119 b.

Distal antenna 116 b may be at least partially surrounded by a dielectric load sleeve 141. Dielectric load sleeve 141 insulates the various portions of the distal antenna 116 b from the surrounding tissue (not explicitly shown) and is configured to provide a uniform diameter between the distal antenna 116 b and the remaining portion of the DAMRAD 110. Dielectric load sleeve 141 may also provide a buffer (i.e., a dielectric buffer) between the distal antenna 116 b and the changing load of the surrounding tissue (not explicitly shown). Distal antenna 116 b may be inserted into the Dielectric load sleeve 141 or dielectric load sleeve 141 may be formed around the distal antenna 116 b by various methods such as injection or by a shrink wrap method commonly used in the art.

FIG. 7 is a cross-sectional illustration of the proximal antenna 116 a of the DAMRAD 110 of FIG. 5. The proximal antenna 116 a is configured as a dipole antenna and includes a proximal antenna distal radiating section 137 and a proximal antenna proximal radiating section 138, both of which receive a microwave energy signal from the proximal antenna feedpoint 119 a at the distal end of the external coaxial cable 120 b. The external coaxial cable 120 b of the triaxial transmission cable 120 includes the outer conductor 123 and the triaxial conductor 125 in a coaxial arrangement and separated by an outer dielectric 124. The external coaxial cable 120 b provides the microwave energy signal to the proximal antenna feedpoint 119 a.

With reference to FIGS. 6 and 7, the outer conductor 123, 123 is common to the internal coaxial cable 120 a and to the external coaxial cable 120 b. Proximal of the proximal antenna 116 a the inner conductor 121, the outer conductor 123 and the triaxial conductor 125 are in a triaxial arrangement. The inner conductor 121 and outer conductor 123 are separated by the inner dielectric 122 and the outer conductor 123 and the triaxial conductor 125 are separated by the outer dielectric 124 and together form the triaxial transmission cable 120.

The triaxial transmission cable 120 supplies a microwave energy signal to the proximal antenna 116 a and to the distal antenna 116 b. The triaxial transmission cable 120 configuration ensures that the feedline distance (e.g., the physical cable distance between the microwave generator 100 of FIG. 1 and the proximal antenna feedpoint 119 a of FIG. 7) is the same for both microwave signals. As such, the microwave signals provided by the internal conductor 120 a and the external conductor 120 b are subject to substantially identical phase shifts caused by the length of the transmission line of the microwave signals.

With reference to FIGS. 5-7, the distal antenna proximal radiating section 115 and the proximal antenna distal radiating section 137 connect to the outer conductor 123 of the triaxial feedline 120. With reference to FIGS. 6 and 7, the proximal antenna feedpoint 119 a and the distal antenna feedpoint 119 b are offset by a distance, wherein the distance between the feedpoints 119 a, 119 b is related to the wavelength of the predetermined microwave frequency, or a fractional portion thereof (i.e., ¼ wavelength, ½ wavelength). The distance may be optimized and/or configured such that the DAMRAD 110 achieves long narrow ablation regions.

As illustrated in FIG. 5, a ferrite ring 179 may also be positioned on the elongated shaft 114 proximal the proximal antenna 116 a to limit the intensity of the microwave energy proximal the proximal antenna 116 a. Ferrite ring 179 may be constructed of any suitable metal or conductible material capable of shunting electromagnetic energy radiating proximally from the antenna 116. Ferrite ring 179 may also be constructed as a Faraday shield and may be configured to shunt electromagnetic energy radiating proximally from the antenna at the predetermined microwave frequency.

Returning to FIG. 7, the distal radiating section of the proximal antenna 137 is at least partially surrounded by a proximal dielectric load sleeve 140. Proximal dielectric load sleeve 140 may be connected to, or be part of, the outer jacket 126, the distal dielectric load sleeve 141 (see FIG. 6) or both.

FIG. 8 is a cross-sectional illustration of the dual-sided choke 128 of the DAMRAD 110 of FIG. 1 in accordance with another embodiment of the present disclosure. The dual-sided choke 128 includes a choke conductor 129 electrically connected to the outer conductor 123. In one embodiment, at least a portion of the choke conductor 129 partially surrounds a portion of the proximal antenna choke extended dielectric 142 and/or the distal antenna choke extended dielectric 143. The distal antenna choke circuit 128 b is formed between the outer conductor 123 and the first segment 129 a of the choke conductor 129, with the opening of the distal antenna choke circuit 128 b being directed toward the distal antenna 116 b. The proximal antenna choke circuit 128 a is formed between the first segment 129 a and the second segment 129 b of the choke conductor 129, wherein the opening of the proximal antenna choke circuit 128 a is directed toward the proximal antenna 116 a. At the dual-sided choke termination point 119, the choke conductor 129 connects to the outer conductor 123 and forms a suitable electrical connection. Electrical connection may be a solder connection, a weld, a press-fit connection or any other suitable connection. The outer surface of the dual-sided choke 128 is coated with the dielectric load sleeve 140 that may be connected to, or formed from, an outer jacket (see FIG. 7, outer jacket 127) a distal dielectric load sleeve (see FIG. 6, dielectric load sleeve 141) or both. Dual-sided choke 128 may be used in conjunction with a ferrite ring (see FIG. 5, ferrite ring 179 positioned on the elongated shaft 114 proximal the proximal antenna 116 a).

The proximal antenna choke circuit 128 a and the distal antenna choke circuit 128 b may be configured as quarter-wave, shorted chokes and may aid in limiting the intensification of the microwave energy beyond the antennas 116 a, 116 b.

In another embodiment, the dual-sided choke 128 of FIG. 8 may be replaced with a double-sided choke 928, as illustrated in FIG. 9. Double-sided choke 928 includes a proximal antenna choke circuit 928 a and a distal antenna choke circuit 928 b. The proximal antenna choke circuit 928 a includes a proximal choke segment 929 a that electrically connects to the outer conductor 123 through the common choke conductor 929. Proximal antenna choke circuit 928 a may at least partially surround the proximal antenna choke extended dielectric 942. The distal antenna choke circuit 928 b includes a distal choke segment 929 b that electrically connects to the outer conductor 123 through the common choke conductor 929. Distal antenna choke circuit 928 b may at least partially surround the distal antenna choke extended dielectric 943. As illustrated in FIG. 9, the proximal antenna choke circuit 928 a and the distal antenna choke circuit 928 b both connect to the outer conductor through the common choke conductor 929. In another embodiment, individual connections to the outer conductor 123 may be provided for each choke circuit 928 a, 928 b. The outer surface of the double-sided choke 928 is coated with the dielectric load sleeve 940 that may be connected to, or formed from, the outer jacket (see FIG. 7, outer jacket 126), the distal dielectric load sleeve (see FIG. 6, distal dielectric load sleeve 141) or both. Double-sided choke 928 may be used in conjunction with a ferrite ring (see FIG. 5, ferrite ring 179 positioned on the elongated shaft 114 proximal the proximal antenna 116 a).

With reference to FIGS. 8 and 9, the longitudinal length of the dual-sided choke 128 is less than the longitudinal length of the double-sided chokes 928. As such, spacing between the proximal antenna 116 a, 916 a and the distal antenna 116 b, 916 b on a device with a dual-sided choke 128 and a dual-sided choke 928, respectively, is different. The spacing between the proximal antenna 116 a, 916 a and the distal antenna 116 b, 916 b affects the phase relationship between the microwave energy radiated from the proximal antenna 116 a, 916 a and distal antennas 116 b, 916 b. As such, a device with a dual-sided choke 128 provides a different phase relationship between the microwave energy radiated from the proximal antenna 116 a and the distal antenna 116 b than a device with a double-sided choke 928.

With continued reference to FIGS. 8 and 9, a device with a double-sided choke 928 may provide a reduction in the overall diameter of the antenna 916 since a dual-sided choke configuration positions one choke radially outward from the other choke while the double-sided choke 928 positions the chokes 928 a, 928 b on substantially identical radial planes.

As various changes could be made in the above constructions without departing from the scope of the disclosure, it is intended that all matter contained in the above description shall be interpreted as illustrative and not in a limiting sense. It will be seen that several objects of the disclosure are achieved and other advantageous results attained, as defined by the scope of the following claims. 

What is claimed is:
 1. A microwave ablation probe, comprising: an elongated shaft including a proximal antenna configured to radiate a first microwave frequency signal and a distal antenna configured to radiate a second microwave frequency signal different than the first microwave frequency signal; and a dual-sided choke disposed between the proximal antenna and the distal antenna, the dual-sided choke includes a proximal antenna choke circuit configured to prevent propagation of the first microwave frequency signal to the distal antenna and a distal antenna choke circuit configured to prevent propagation of the second microwave frequency signal to the proximal antenna.
 2. The microwave ablation probe according to claim 1, further comprising: a feedline operably coupled to the elongated shaft, the feedline including a first conductor, a second conductor, and a third conductor.
 3. The microwave ablation probe according to claim 2, wherein the feedline is arranged in a triaxial configuration in which the first conductor is an inner conductor, the second conductor is a middle conductor coaxially disposed over the inner conductor, and the third conductor is an outer conductor coaxially disposed over the middle conductor.
 4. The microwave ablation probe according to claim 2, wherein the first conductor and the second conductor are coupled to the proximal antenna and the second conductor and the third conductor are coupled to the distal antenna.
 5. The microwave ablation probe according to claim 2, wherein the dual-sided choke is coupled to the second conductor.
 6. The microwave ablation probe according to claim 1, wherein a length of at least one of the proximal antenna, the distal antenna, or the dual-sided choke is related to one-quarter of a wavelength of one of the first microwave frequency signal or the second microwave frequency signal.
 7. The microwave ablation probe according to claim 1, wherein the proximal antenna and the distal antenna are configured to radiate the first microwave frequency signal and the second microwave frequency signal simultaneously.
 8. The microwave ablation probe according to claim 1, further comprising a dielectric coating disposed at least partially over at least one of the proximal antenna, the distal antenna, or the dual-sided choke.
 9. The microwave ablation probe according to claim 1, wherein the proximal antenna further includes a distal radiating section and the distal antenna further includes a proximal radiating section, wherein the distal radiating section and the proximal radiating section are configured to radiate microwave energy between a distal end of the proximal antenna and a proximal end of the distal antenna.
 10. The microwave ablation probe according to claim 9, wherein the proximal radiating section and the distal radiating section have a length proportional to a wavelength of at least one of the first microwave frequency signal or the second microwave frequency signal.
 11. The microwave ablation probe according to claim 1, wherein the proximal antenna includes a first feedpoint and the distal antenna includes a second feedpoint separated by a distance that is related to a quarter wavelength of at least one of the first microwave frequency signal or the second microwave frequency signal.
 12. A method for ablating tissue, comprising: transmitting a first microwave frequency signal to a proximal antenna of an ablation probe; transmitting a second microwave frequency signal different than the first microwave frequency signal a distal antenna of the ablation probe; preventing propagation of the first microwave frequency signal to the distal antenna through a proximal antenna choke circuit of a dual-sided choke disposed between the proximal antenna and the distal antenna; and preventing propagation of the second microwave frequency signal to the proximal antenna through a distal antenna choke circuit of the dual-sided choke.
 13. The method according to claim 12, wherein the first microwave frequency signal and the second microwave frequency signal are transmitted simultaneously.
 14. The method according to claim 12, wherein the first microwave frequency signal and the second microwave frequency signal are transmitted alternatively. 